|Publication number||US7514122 B2|
|Application number||US 11/582,703|
|Publication date||Apr 7, 2009|
|Filing date||Oct 17, 2006|
|Priority date||Jun 12, 2001|
|Also published as||US7163715, US7201940, US7854958, US20070036905, US20070166496, US20070184228, US20090176005|
|Publication number||11582703, 582703, US 7514122 B2, US 7514122B2, US-B2-7514122, US7514122 B2, US7514122B2|
|Inventors||Pamela A. Kramer|
|Original Assignee||Advanced Cardiovascular Systems, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (104), Non-Patent Citations (99), Referenced by (25), Classifications (74), Legal Events (4)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a divisional of U.S. application Ser. No. 10/331,838, filed Dec. 30, 2002, now U.S. Pat. No. 7,163,715, which is a continuation-in-part of U.S. application Ser. No. 09/880,514, filed Jun. 12, 2001, now U.S. Pat. No. 7,201,940, the contents of each of which are hereby incorporated herein by reference.
This invention relates to medical devices, and more particularly to methods of manufacturing and coating medical devices utilizing thermal spray processing and cold spray processing. The medical devices may be made porous to act as a functional drug delivery vehicle.
Several interventional treatment modalities are presently used for heart disease, including balloon and laser angioplasty, atherectomy, and by-pass surgery. A focus of recent development work in the treatment of heart disease has been directed to endoprosthetic devices referred to as stents. Stents are generally cylindrically shaped intravascular devices that are placed within an artery to hold it open. The device can be used to reduce the likelihood of restenosis and to maintain the patency of a blood vessel immediately after intravascular treatment. In some circumstances, a stent can also be used as the primary treatment device where the stent is expanded to dilate a stenosis and then left in place.
Many medical devices, including stents, are manufactured from commercially available metals and metal alloy substrates, such as stainless steel and cobalt based alloys, configured as tube stock, wherein the substrate typically has average grain sizes ranging from approximately 0.0025 inch (64 microns), ASTM grain size 5, to around 0.00088 inch (22 microns), ASTM grain size 8. These grain sizes typically result in about two to five grains across the thickness of the device. Part of the limitation in achieving a finer grain size with metals and metal alloys arises from the number of draws and anneals the substrate must go through to achieve its final size. Stents and other medical devices (such as guide wires, ring markers, pacemaker lead tips, and catheters) may benefit from a reduction in grain size of the substrate.
Intravascular interventional devices, such as stents, are typically implanted within a vessel in a contracted state, and expanded when in place in the vessel in order to maintain the patency of the vessel. Such medical devices may have a metallic support structure to provide the strength required to maintain the patency of the vessel in which it is to be implanted so as to allow fluid flow through the vessel. Such metallic medical devices are often provided with an exterior surface coating with the purpose of providing a more biocompatible and/or hemocompatible surface. Since it is often useful to provide localized therapeutic pharmacological treatment of a blood vessel at the location being treated with the medical device, it has been the practice within the medical industry to configure such implantable medical devices with a coating of a polymeric material having the capability of being loaded with antiproliferative drugs and other therapeutic agents. Such polymer coated medical devices provide for the placement and release of therapeutic drugs at a specific intravascular site, but are relatively expensive and difficult to manufacture using conventional processes.
What has been needed and heretofore unavailable in the art of manufacturing medical devices, such as stents, configured from commercially available biocompatible materials, such as stainless steel and cobalt-based alloys, are methods for forming porous implantable medical devices and for forming a porous coating on consolidated medical devices. In addition, it would be desirable to form drug-eluting medical devices without the need for coating the substrate with a polymer. The present invention meets these and other needs.
The present invention relates to methods of manufacturing porous medical devices utilizing thermal spray processing and cold spray processing. Conventional spray processes are adapted to manufacture porous substrates and coatings that may be constructed as tube stock, metallic sheet, wire or near net-shaped configurations for forming drug-eluting medical devices, such as, but not limited to, stents, anastomosis clips, embolic protection filters, graft attachment systems, ring markers, guide wires, mitral valve repair devices, tubular or wire based implants, defibrillator or pacemaker lead tips, and catheters or other delivery system devices. As part of the spray process or as a separate aspect of the method of manufacture of the medical device, a therapeutic agent or drug may be applied to the porous coating or substrate.
Thermal spray processing and spray processing provide methods for manufacturing a porous medical device for use as a drug delivery vehicle in three ways: by forming porous starting materials, by spraying consolidated starting materials with a porous coating, and by spraying near net-shaped medical devices with a porous coating. Current thermal and cold spray processes inherently include a degree of porosity that are supplemented with post-processing techniques that provide full consolidation of the sprayed material. However, the present invention takes advantage of the spray process to create a desired level of porosity so as to produce substrates and coatings that can elute a drug. The spray process may incorporate a wide variety of materials, such as metals, metal alloys, polymers, ceramics, cermets and composites. Furthermore, the conditions of the spray process may be varied to achieve desired properties for a particular material, for example, to minimize oxidation or other contamination. In addition, the present invention provides for the manufacture of a medical device configured for drug delivery without the need for triple-coating the substrate with a polymer. Thus, a polymer topcoat may or may not be needed with porous medical devices manufactured by spray processes of the present invention.
Hypotubing or other tube stock manufactured using the spray processes of the present invention may be configured into a stent or other tubular medical device. The porous medical device may then be impregnated with a therapeutic agent or drug via known or to be developed transport mechanisms, such as soaking in a solution having an effective concentration of the drug or agent. The spray process may be designed to provide a multiple gradient of porosity through and/or within the material, e.g., denser on the outer diameter of a stent so the drug releases preferentially into the artery wall, or denser then more porous then denser again through the device thickness to allow the material itself to act as a diffusion barrier for the release of the drug. The process could also potentially spray different materials into the different layers, so long as the corrosion and mechanical properties of the manufactured stent were not adversely affected. For example, the base layer of the medical device could be metallic with an outer layer being formed from a sprayed ceramic, wherein either the base layer and/or the coating may be porous.
Alternatively, a spray process of the present invention may be used to coat existing tube stock or starting materials for further processing into a medical device, such as a stent. This inventive coating process has the advantage that soaking the porous coated medical device in a drug would limit the drug coating to the outer diameter only of the medical device, thereby minimizing drug release into the bloodstream. The coating may be composed from a material of the same composition as the underlying substrate or may be composed of a different material, such as a ceramic, hat would not adversely affect the corrosion or mechanical functionality of the end product. One aspect of the present invention contemplates that the drug-eluting edical device is formed at least in part of a metallic material, for example, iron, obalt, platinum, titanium, and their alloys.
Another aspect of the present invention includes coating a near net-shaped medical device formed by conventional manufacturing methods. A coating formed by the spray process of the present invention may be metallic, ceramic, or any other material that can undergo the thermal or cold spray process successfully. Such a coated medical device may be impregnated with a therapeutic agent or drug via a known or to be developed transport mechanism. A drug or agent that could withstand the temperature/pressure of the spray process could be sprayed directly onto the medical device with the coating material. A further aspect of the present invention includes using the spray process to form functionally graded coatings so that the sprayed material acts as a controlling diffusion barrier to drug release. The process may provide an all-over coating or a coating focusing only on the outer diameter and sidewalls of the medical device, thereby allowing preferential focusing of the delivery of a drug or therapeutic agent.
The therapeutic agents and drugs that may be loaded into the drug-eluting porous medical device of the present invention can include antiplatelets, anticoagulants, antifibrins, antiinflammatories, antithrombins, and antiproliferatives. Such drugs and agents are most often used to treat or prevent restenosis, and are provided by way of example and are not meant to be limiting, since other types of therapeutic agents which are equally applicable for use with the present invention may be incorporated in a porous medical device formed by spray processing.
Other features and advantages of the invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way of example, the features of the invention.
The present invention relates to use of various spray processes for forming porous starting materials and porous near net-shaped medical devices, and to provide a porous coating on starting materials or near net-shaped medical devices. In accordance with the present invention, thermal spraying and/or cold spraying may be used to partially or wholly form starting materials, such as, but not limited to, tube stock, substrate sheets and wire, which can be further processed into a net-shaped (finished) medical devices. Similarly, thermal spraying and/or cold spraying may be used to coat starting materials or to coat near-net-shaped medical devices, such as, but not limited to, stents, anastomosis clips, embolic protection filters, graft attachment systems, markers, guide wires, mitral valve repair devices and defibrillator lead tips. As part of the spray process or as a separate aspect of the method of manufacture of the medical device, a therapeutic agent or drug may be applied to the porous coating or substrate. While virtually any medical device that is implanted or used in the body will benefit from the present invention, the embodiments disclosed herein as applied to stents are intended as only examples and are not meant to be limiting.
Spray processing (thermal spraying and cold spraying) provides methods for manufacturing a porous medical device for use as a drug delivery vehicle in three ways: (1) creating porous tube stock (e.g., hypotubing) or other starting material via thermal or cold spraying; (2) spraying pre-existing starting materials (e.g., tube stock or metallic sheets) with a porous coating; and (3) spraying pre-existing medical devices (e.g., stents) with a porous coating. The various spray processes can utilize a wide variety of materials, and the conditions of the process may be varied depending on the material to minimize oxidation or other contamination. As used herein, thermal spray processing refers to a group of known metallurgical spray processes, such as, but not limited to, combustion (wire and powder), arc wire, high velocity oxy-fuel (HVOF), plasma and detonation (see
Both the processes of thermal spraying and cold spraying inherently have porosity as a difficulty to overcome, and while current methods allow up to full (one-hundred percent) consolidation of the sprayed material, the present invention produces a porous coating or porous substrate that can elute a drug or therapeutic agent. A potential exists for drug co-spraying with the coating or substrate material, so long as the drug does not degrade at the high temperatures and/or velocities used in the spray process. As desired, a polymer or similar topcoat to protect or control the release of the therapeutic agent or drug could be applied to the medical device via a spray process, so long as the polymer would not degrade from the processing.
Starting materials, such as tube stock (hypotubing) or substrate sheets may be manufactured using a spray process. The starting material may then be processed into a medical device (stent), and the porous material may be impregnated with a therapeutic agent or drug via known or to be developed transport mechanisms, such as soaking in or spraying with a solution having an effective drug or agent concentration. For purposes of the present invention, the term “impregnate” means to fill throughout or to saturate. The spray process may be varied to allow a multiple gradient of porosity through and/or within the material, e.g., denser on the inner diameter or layers (so the drug releases preferentially into the artery wall for a stent), or denser—then more porous—then denser again to allow the material itself to act as a diffusion barrier for the release of the therapeutic agent or drug. The process could also potentially spray different materials into the different layers, so long as the corrosion and mechanical properties of the manufactured medical device were not adversely affected. For example, the base layer(s) of the medical device could be formed from a metal or alloy, while the outer layer(s) of the medical device may be formed from a ceramic material.
The spray process of the present invention may also be used to coat existing starting materials for medical devices, such as tube stock, hypotubing and sheets of a substrate material for further processing into a medical device, such as a stent. Use of a spray process has the advantage that soaking the porous coated medical device in a therapeutic agent or drug would limit the drug or therapeutic agent to the outer surface of the medical device, minimizing release of the drug or agent into the bloodstream. The coating may be made from a material of the same composition of the underlying starting material (e.g., a metallic alloy), or may be made from other material (e.g., a ceramic) that would not adversely affect the corrosion or mechanical functionality of the end product. As with forming starting materials, the spray process of the present invention could be used to produce functionally graded coatings (e.g., different degrees of density and porosity) so as to allow the coating material to create a diffusion barrier to control the release of the therapeutic agent or drug.
The spray process of the present invention may be used to coat a near net-shaped medical device, such as an existing stent. Such a coating could be metallic, ceramic, composite, polymeric or any other material that can undergo the spray process successfully. The coated medical device would then be impregnated with a drug or therapeutic agent via known or to be developed transport mechanisms. Alternatively, the drug or agent could be co-sprayed with the coating material, so long as there is minimal resulting degradation. Thus, a therapeutic agent or drug that could withstand the temperature and pressure of the spray process could be applied directly onto the existing medical device with the coating material. A special fixture may be constructed to hold the medical device and prevent damage during the coating process. As with coating starting materials, the spraying could be functionally graded to allow the material to act as a controlling diffusion barrier to drug release. The spraying could consist of an all-over coating or a coating focusing only on the outer surface or diameter of the medical device and any sidewalls when an inert material, such as a ceramic were used, allowing preferential focusing of the drug delivery. For example, a stent made from 31 6L stainless steel could be layered with a porous coating of a ceramic and then impregnated with paclitaxel. The drug coated stent could then be further coated with a protective polymer layer.
As used herein, spray processing describes a broad class of related processes in which molten (or semi-molten) droplets or fine particles of a metal, metal alloy, ceramic, glass, polymer and/or other suitable material are (1) sprayed to form a starting material (e.g., a tube stock or flat sheet); (2) sprayed onto a surface of a previously formed substrate material (e.g., hypotube or sheet metal) to produce a coating; or (3) sprayed onto a near-net-shape product. The spray process provides the medical device with unique properties, such as strain-tolerant composites or porous materials susceptible to impregnation with a therapeutic agent or drug. Deposition rates via spray processes are very high in comparison to alternative coating technologies, providing deposit thicknesses commonly in the range of about 0.1 to 1.0 millimeter (mm). Furthermore, thicknesses greater than one centimeter (cm) can be achieved with some materials. Two types of spray process compatible with the present invention include thermal spray processing and cold spraying.
Some advantages of using a spray process to form a porous medical device include the versatility with respect to feed materials (metals, ceramics, and polymers in the form of wires, rods, or powders); the capacity to form barrier and functional coatings on a wide range of substrates; the ability to create freestanding structures for net-shape manufacturing of high performance ceramics, composites, and functionally graded materials; and the rapid solidification synthesis of specialized materials. Further, the spray process can be used to manufacture a net or near net-shaped medical device, such that the product resulting from the spray process is close to or at the desired size and shape of the final product. Spray processing is presented here both with and without post-processing of the sprayed material.
There are many possible variations of known spray process for forming porous starting materials and porous coatings resulting in medical devices of the present invention. Because porous starting materials and coatings may be used in conjunction with medical devices that are generally cylindrical in shape, the spray processes may incorporate either a moving spray gun and/or a moving mandrel or substrate so as to uniformly disperse material onto the mandrel to form the porous starting material or porous coating. The spray processes used in the present invention may be enhanced through the use of a precision computer controlled apparatus.
Another benefit of using a spray process to manufacture a medical device is that the spray process may be used to form porous tube stock on top of a removable mandrel. The porous tube stock formed by a spray process can be used in place of a gun drilled or extruded rod, and eliminates the need for subsequent tube manufacturing.
The thickness of the tube stock may be varied by spraying more or less material, and the inner diameter dimensions may be varied by changing the size of the mandrel. The inner mandrel may be made of a substance that melts out, or that is coated with a substance that allows easy removal of the finished sprayed tube stock. If the grain size, porosity, and dimensional tolerances (including wall runout, wall thickness, concentricity and surface roughness) are within specifications, the mandrel may be removed and the sprayed tube stock may subjected to further processing into a stent or other tubular or ring-shaped product. To create a ring-shaped product from a tube stock, the tube is sprayed to the desired dimensions and then cut in the transverse direction to result in rings of the desired size.
For removal of the porous tube stock after it is formed, it may be beneficial to either melt or shrink the mandrel's diameter to ease removal of the tube stock. For example, the mandrel can be formed of metal that will shrink in diameter when cooled, while the tube stock may be heated so that it expands radially outwardly. The mandrel can then be easily removed from the tube stock. The mandrel and tube stock may also both be heated so that the difference in expansion rates may cause separation between the two. The mandrel may also be removed from the tube stock by a process called “cross-rolling.” The tube stock, with the mandrel inside, can be run through a series of crossed rollers that will flex the tube stock and impart a separation between the tube and the mandrel, which is then easily removed. Alternatively, the mandrel could be lubricated so as to provide a low friction surface from which to slide the off tube stock.
Any of several known or to be developed post-processing operations may be performed on a porous tube stock formed from a spray process so as to improve or otherwise modify grain size, porosity, and final dimensions and tolerances of the sprayed tube stock. The inner diameter dimensions and surface finish of the porous tube stock may be dependant on the mandrel that is used. If the starting size of the sprayed tube is large enough, it may be desirous to bore and ream or just ream the inner diameter for both dimension and surface roughness improvement. A drawing operation may be performed on the sprayed tube to achieve the desired final size. In addition, if the outer diameter is too rough, the tube stock may be machined or ground prior to the drawing operation. Further, the tube stock may be mechanically processed or swaged before the tube stock is removed from the mandrel in order to develop desired mechanical properties. After the tube stock is removed from the mandrel other post processing includes exerting high mechanical pressures onto the stent in order to develop the desired mechanical properties and tempering and hardening the tube stock with traditional heat treating mechanisms known in the art. For correct sizing, the outer diameter and/or the inner diameter of the tube stock can be machined, reamed, ground, or drawn to size after being removed from the mandrel. The grain size of the porous tube stock may be decreased by reducing the required number of heat-processing steps or by reducing the starting size of the raw material that is spray processed to form the tubing.
Any of several known or to be developed post-processing operations may also be performed on a porous coating formed on a medical device from a spray process so as to improve or otherwise modify grain size, porosity, and final dimensional tolerances of the sprayed medical device. Further, the thickness of the coating may be varied by spraying more or less material, and may be varied along the length and around the diameter of the object to be-coated. If a porous coating is formed by spray processing the inner diameter of tube stock or other tubular near net-shaped devices (such as stents), then post-processing may include modifying the inner diameter dimensions and surface roughness by, for example, boring and/or reaming. If the porous coating is formed by spray processing an outer wall or surface of the medical device, post-processing may include machining (e.g., centerless grinding) or drawing to reduce coating thickness variability and to improve the surface finish. When the grain or node size, material density, porosity and dimensional tolerances of the porous coating are within desired specifications, the porous coated medical device may be subjected to post-passivation or other desired post spray processing steps when the coating process is an intermediate step in finishing the medical device.
While spray processing may be used to manufacture near-net shape medical devices, the variability in the spray process may require post-processing so that the product achieves the required dimensional tolerances. Any of several known or to be developed post-processing operations may be performed on a porous medical device formed from a spray process so as to improve or otherwise modify grain size, porosity, and final dimensional tolerances of the sprayed medical device. Such processing may include machining, centerless grinding, heat treating or other surface processing of the outer wall or surface of the sprayed medical device to reduce wall thickness variability and to improve the surface finish.
Two aspects of using spray processing to create porous medical devices of the present invention include (1) controlling the grain size of the sprayed material, and (2) controlling the degree of porosity in the sprayed substrate or coating.
The grain size or node size of the sprayed material used in porous starting materials or sprayed porous coatings resulting from the present invention depends on numerous factors, including the size of the particles being sprayed; the grain size of the particles; the formation, impact and rate of solidification of the sprayed particles; and the length of time the particle material is heated above a temperature that allows significant grain growth. Grain-size strengthening is where there is an increase in strength of a material due to a decrease in the grain size. A larger grain-boundary area resulting from smaller grain sizes more effectively blocks dislocation movement. The type and amount of working required to achieve a desired grain size depends on the material being sprayed, for example, ceramics may require a high temperature working step, and metals and composites may be workable at room temperature.
For a metallic tube, if the grain size is larger than desired, the tube may be swaged to introduce heavy dislocation densities, then heat treated to recrystallize the material into finer grains. Alternatively, different material forms may be taken through a drawing or other working and heat treating process to recrystallize the tubing. The outer diameter of the tube usually requires a machining step to smooth the surface after the swaging process, and the same may be true before the tubing can be properly drawn.
For a metallic coating, one modification to grain size that may be made is to heat-treat the coating to control grain growth. For example, it may be desirable to spray a metallic coating onto a target substrate, heat the coating, and then grow the metallic grains in the coating. Similarly, the porous coated substrate may be mechanically processed or swaged, annealed, heat-treated, or cross linked in order to develop desired mechanical properties. Generally, it is difficult to work a porous, coated substrate in a way that introduces a high dislocation density that may then be used to recrystallize the material. For a spray coated metallic wire or tubing, the wire or tubing may be swaged or drawn to produce a higher dislocation density, then annealed to recrystallize to a smaller grain size. Porous ceramic coatings formed from a spray process may require post-processing heating to control grain size; whereas, porous polymeric coatings may require further cross-linking.
Lowering the grain size and increasing the number of grains across the thickness of the porous medical device allows the grains within the medical device to act more as a continuum and less as a step function. For example, spray processing 31 6L stainless steel to a smaller grain size may result in an average grain size of between approximately one and sixty-four microns, with a subsequent average number of grains across the strut thickness about eight or greater. With a well controlled spray process, it is possible to reduce the average grain size of a porous medical device formed from spray processed 31 6L stainless steel to between one and ten microns.
The mechanics and chemistry of spray processing inherently results in small voids (porosity) in the sprayed material. The porosity of the sprayed material may be maximized, minimized, eliminated or controlled to a desired level through adjustment of the spray process parameters, such as particle size, temperature, pressure, injection velocity and co-spraying with a binder material that may be subsequently removed. In addition, the porous medical device may be post-processed to further control the size and distribution of the pores and voids. One such method of post processing to control porosity is to process the material under high mechanical pressure in a vacuum to sinter the grains together, as is generally used for powder processing. Additional methods to control porosity include co-spraying with varying amounts of a binder material that may be removed through subsequent operation, such as sublimation or soaking in a solvent.
The process of manufacturing porous starting materials, porous coatings and porous near net-shaped medical devices in accordance with the present invention requires selecting a spray process method and apparatus, such as cold spraying, combustion spraying, arc spraying, high velocity oxy-fliel spraying and plasma spraying. The spray process selected must be compatible with the material to be sprayed, such as metals, alloys, polymers, ceramics, and cermets. Similarly, the same or an additional spray process could be selected for spraying of a drug or therapeutic agent, such as antiplatelets, anticoagulants, antifibrins, antiiflammatories, antithrombins, and antiproliferatives.
As shown in
Materials used in the spray process can include elements (e.g., metals), metallic alloys (e.g., iron-based, cobalt-based, titanium-based), ceramics, composites, cermets and polymers. Suitable biocompatible materials for use in forming medical devices using the spray process of the present invention include, but are not limited to, elements and alloys of titanium, tungsten, tantalum, vanadium, gold, silver, palladium, platinum and iridium. Certain biocompatible metal alloys that have been used in forming medical devices include:
(1) iron-carbon alloys, e.g., ASTM F 138, ASTM P139, AISI 31 6L (18Cr-14Ni-2.5 Mb);
(2) cobalt-chromium alloys, e.g., ASTM F90 (Co-2OCr-20W-1ONi) [available as trade name products HAYNES 25 (Haynes) and L-605 (Carpenter)], ASTM F562 (35Co-35Ni-2OCr-1OMo) [available as trade name product MP35N(SPS Technologies)], ASTM F 1058 (4OCo-2OCr-1 6Fe-1 5Ni-7Mo) [available as trade name products ELGILOY (Elgin) and PHYNOX (Imphy Ugine Precision)], HAYNES 188 (Haynes) (Co-24Ni-23Cr-15W); and
(3) nickel-titanium alloys, e.g., ASTM F2063 [nitinol available from Wah Chang and Special Metals].
Suitable biocompatible polymers that may be used in the spray process as part of the substrate, coating or topcoat include, but are not limited to polymethyl-methacrylate (PMMA), ethylenevinylalcohol (EVAL), polybutylmethacrylate (PBMA), biodegradable polymers [such as polyglycolic acid (PGA) and polyL-lactic acid (PLLA)], copolymers and blends thereof.
Various therapeutic agents, drugs and other pharmacologic compounds may be applied to the porous substrate or porous coating to control local thrombosis and restenosis. Classes of such compounds include, but are not limited to, substances that are antiproliferative, antithrombogenic, antineoplastic, antiinflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, and antioxidant. Specific examples of therapeutic agents or drugs that are suitable for use in accordance with the present invention include taxol, paclitaxel, docetaxel, sirolimus, everolimus, actinomycin D (ActD), prostaglandins, aspirin or derivatives and analogs thereof.
Examples of antiplatelets, anticoagulants, antifibrins, and antithrombins include, but are not limited to, sodium heparin, low molecular weight heparin, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogs, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein Jib/lila platelet membrane receptor antagonist, recombinant birudin, thrombin inhibitor (available from Biogen located in Cambridge, Mass.), and 7E-3B (an antiplatelet drug from Centocor located in Malvern, Pa.). Examples of antimitotic agents include methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, adriamycin, and mutamycin.
Examples of cytostatic or antiproliferative agents include angiopeptin (a somatostatin analog from Ibsen located in the United Kingdom), angiotensin converting enzyme inhibitors such as CAPTOPRIL (available from Squibb located in New York, N.Y.), CILAZAP'RIL (available from Hoffman-LaRoche located in Basel, Switzerland), or LISINOPR.IL (available from Merck located in Whitehouse Station, N.J.), calcium channel blockers (such as nifedipine), coichicine, fibroblast growth factor (“FGF”) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, LOVA-STATIN (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug from Merck), methotrexate, monoclonal antibodies [such as platelet-derived growth factor (“PDGF”) receptors], nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitor (available from GlaxoSmithKline located in United Kingdom), seramin (a PDGF antagonist), serotonin blockers, steroids, thioprotease inhibitors, triŕzolo-pyrimidine (a PDGF antagonist), and nitric oxide. Other therapeutic drugs or agents which may be appropriate include alpha-interferon, genetically engineered epithelial cells, and dexamethasone.
While the foregoing therapeutic agents have been used to prevent or treat restenosis, they are provided by way of example and are not meant to be limiting, since other therapeutic drugs may be developed which are equally applicable for use with the present invention. The treatment of diseases using the above therapeutic agents are known in the art. The calculation of dosages, dosage rates and appropriate duration of treatment are previously known in the art. Furthermore, the therapeutic drugs or agents are applied to the porous substrate or coating or as part of the spray process at desired concentration levels per methods well known in the art.
As mentioned above, spray processing includes several variants of the apparatus and spraying method, such as cold spraying, combustion spraying, arc spraying, high velocity oxy-fliel spraying and plasma spraying. The following is a brief summary of the basic components and functions of several of the spray processes that may be used to manufacture porous starting materials, coatings and near net-shaped medical devices in accordance with the present invention.
As shown in
The cold spray process involves minimal heat input to the feedstock powder or the substrate, thus making it possible to deposit thermally sensitive as well as conventional materials. The process generally produces high density, low residual stress deposits with low oxide contents. When the cold spray process is used to produce a consolidated coating or substrate, an average grain size of between one and sixty-four microns may be achieved. Alternatively, the cold spray process parameters may be controlled to produce porous coatings and substrates that are suitable as a drug delivery vehicle. In addition, a robust drug or therapeutic agent may be co-sprayed with the biocompatible material.
Cold spray processing may be used to project biocompatible materials onto a surface at relatively lower temperatures than used in thermal spray processing, and the materials typically are not sprayed in a molten or semi-molten state. Instead, the biocompatible material is sprayed as powder particles, which are introduced from a feeder into a high pressure gas (1.5 to 2.5 MPa) where both the gas and particles enter a supersonic nozzle or jet. The particle size may range from about one to sixty-four microns for consolidated spray coatings, and may be varied to achieve a desired degree of porosity. The gas is typically heated to a temperature from about 380° to 420° Celsius. Suitable gases for creating a jet stream (300-1500 m/sec) with the powder particles include, but are not limited to, air, nitrogen (N2), oxygen (O2), helium (He), argon (Ar), xenon (Xe), and carbon dioxide (CO2). The jet stream is directed against a mandrel or substrate positioned about eight to ten millimeters from the nozzle so as to coat the mandrel or substrate with particle splats, as shown in
Typical values for tensile adhesion of consolidated cold spray coatings are in the range of 30-80 MPa (4.4-11.6 ksi), with porosities in the range of one to ten volume percent, deposit thicknesses ranging from ten microns to ten millimeters, deposition rates in the range of 0.0 10 to about 0.080 m3 per hour, and deposition efficiencies in the range of fifty to eighty percent. Several considerations when using a cold spray process include the dependency of porosity on the ambient spray environment, powder characteristics (e.g., particle size and size distribution), and thermal-spray parameters (e.g., powder level, gas-flow features, and spray distance). The spray environment will have a significant influence on, for example, the oxidation of metals, leading to greater porosity.
As shown in
As shown in
As shown in
Another known HVOF system uses a simpler combination of a high pressure combustion nozzle and an air cap. Fuel gas (e.g., propane, propylene or hydrogen) and oxygen are supplied at high pressure, and combustion occurs outside the nozzle and within an air cap supplied with compressed air. The compressed air pinches and accelerates the flame, and acts as a coolant for the gun. Biocompatible material in powder form is fed at high pressure axially from the center of the nozzle towards a mandrel or near net-shaped medical device so as to deposit a spray-formed substrate or coating.
Benefits of HVOF include high particle velocity, low particle temperatures, and reduced time at temperature during the spraying process, which reduces oxidation and degradation of the constituents. The temperature of a target near net-shaped medical device can be maintained relatively low during processing, thereby avoiding damage, metallurgical changes and distortion to the substrate material. The parameters of the HVOF spray process (e.g., temperature, particle size, and gas velocity) can be adjusted to control the porosity of the spray-formed substrate or coating. In addition, a robust drug or therapeutic agent able to withstand the high temperatures and velocities used in the process may be co-sprayed with the biocompatible material.
The plasma spray apparatus (gun) may be constructed of a copper anode and tungsten cathode, both of which may be water cooled. Plasma gas (e.g., argon, nitrogen, hydrogen, helium) flows around the cathode and through the anode, which is shaped as a constricting nozzle. The plasma is initiated by a high voltage discharge, which causes localized ionization and a conductive path for a direct current (DC) arc to form between cathode and anode. The resistance heating from the arc causes the gas to reach extreme temperatures, dissociate and ionize to form plasma. Typically, plasma generation begins at 10,000 F, and most plasma guns maintain an internal temperature between 15,000° F. and 30,000° F. The plasma exits the anode nozzle as a free or neutral plasma flame (i.e., plasma that does not carry electric current). When the plasma is stabilized and ready for spraying, the electric arc extends down the nozzle, instead of shorting out to the nearest edge of the anode nozzle. This stretching of the electric arc is a result of a thermal pinch effect.
Due to the tremendous heat generated with this thermal spray process, the plasma gun components must be constantly cooled with water to prevent the gun from melting. Water may be sent to the gun through the same lines as electrical power. Small temperature changes in the cooling water may affect the ability to produce high quality, plasma generated spray coatings and substrates. Accordingly, a water chiller can be used to help produce high quality porous medical devices. Cold gas around the surface of the water-cooled anode nozzle, being electrically non-conductive, constricts the plasma arc, raising its temperature and velocity. Powder is fed into the plasma flame most commonly via an external powder port mounted near the anode nozzle exit. The powder is so rapidly heated and accelerated that spray distances can be on the order of twenty-five to one hundred-fifty millimeters. Benefits associated with a plasma spray process include a high degree of flexibility, a large choice of substrate and coating materials, high production spray rates, and automation of the process.
As shown in
Referring now to
In one embodiment as shown in
For use in coronary arteries, the stent diameter must be very small, so the tube stock from which it is made must necessarily also have a small diameter. Typically, the stent has an outer diameter on the order of about 0.03 inch (0.75 mm) to about 0.06 inch (1.5 mm) in the unexpanded condition, equivalent to the tubing from which the stent is made, and can be expanded to an outer diameter of 0.10 inch (2.5 mm) or more. The wall thickness of the tubing is about 0.002 inch (0.05 mm) to about 0.01 inch (0.25 mm). As with the foregoing stent dimensions, all of the medical devices that can be formed utilizing the present invention can vary substantially in size and shape so that the disclosed dimensions and shapes are representative examples only and are not meant to be limiting.
The spray process of the present invention may also be used to form an anastomosis device (clip) 40, as shown in
Referring now to
Referring now to
In many such grafts 90, such as those used for repairing an abdominal aortic aneurysm, the upper body may include a first attachment system 100 positioned proximate an upper (wider) opening of the graft. Tube grafts may contain a like attachment system at the lower openings of the graft. Similarly, bifurcated grafts may include smaller attachment systems 102 positioned at the end of the legs and proximate the lower (narrower) openings of the graft. Such attachment systems may be of various configurations, such as, but not limited to, a ring and link design, a zigzag design, a coil design, a slotted tube design or a tubular mesh design. As heretofore described regarding stents (
The illustrative stent 10 of the present invention and similar medical device structures can be made-in many ways. One method of making such a stent is to cut tube stock or sheets of substrate formed according to the method and devices of the present invention so as to remove portions of the tube stock in the desired pattern for the stent, leaving relatively untouched the portions of the tube stock that are to form, for example, the cylindrical rings 12 and links 13. Various processes of forming the desired stent pattern are available and are known in the art, such as, but not limited to, using laser or chemical etching, electronic discharge machining and stamping.
A machine-controlled laser system 20 may be used to cut a desired pattern in a spray-formed or spray-coated tube stock 21, as illustrated schematically in
Cutting a fine structure, such as a stent 10, via a machine-controlled laser 20 requires minimal heat input and the ability to manipulate the tube stock 21 with precision. It is also necessary to support the tube stock, yet not allow the tube stock to distort during the cutting operation. To achieve a relatively small geometry of a desired stent pattern formed with ring struts 12 and links 13 sized for human vasculature, it is necessary to have very precise control of the laser's power level, focused spot size and positioning of the laser cutting path, which is well known in the art.
Referring now to
The delivery of the stent 10 is accomplished in the following manner. The stent is first mounted onto the inflatable balloon 14 on the distal extremity of the delivery catheter 11. The catheter-stent assembly is introduced within the patient's vasculature in a conventional Seldinger technique through a guiding catheter (not shown). A guidewire 18 is disposed across the damaged arterial section, and then the catheter/stent assembly is advanced over the guidewire within the artery until the stent is directly within the target site. As stated, the manufacture of guidewires also will benefit from the spray processes of the present invention. While the drawing figures illustrate a rapid exchange (Rx) intravascular catheter and guidewire, medical devices of the present invention may be also used with an over-the-wire (OTW) intravascular catheter. Additionally, although a balloon expandable stent and associate catheter assembly are depicted, a self-expanding stent in combination with an appropriate alternative catheter assembly may be used.
Once the stent 10 is positioned at the desired location, the balloon 14 of the catheter 11 is expanded, forcing the stent against the wall of the artery 15, as illustrated in
The stent 10 serves to hold open the artery 15 after the balloon 14 is deflated and the catheter 11 is withdrawn, as illustrated by
While several particular forms of the invention have been illustrated and described, it will also be apparent that various modifications can be made without departing from the scope of the invention.
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|U.S. Classification||427/421.1, 428/34.1, 427/446, 427/189, 428/547, 428/587, 427/448, 428/36.5, 428/586, 427/447, 427/455, 427/427.1, 623/1.39, 623/1.15|
|International Classification||B22F3/115, B05D7/00, B05D1/08, A61F2/06, B29D22/00, B05D1/02, C23C4/02, B29B15/10, B22F5/12|
|Cooperative Classification||Y10T428/1376, Y10T428/12292, Y10T428/139, Y10T428/12021, Y10T428/12299, Y10T428/13, C23C4/12, C23C28/028, A61L29/16, B05B7/226, A61L31/088, A61L27/306, C23C28/36, C23C28/321, A61L2300/416, C23C24/04, C23C28/322, B05B7/224, A61L2300/606, A61L31/16, A61L29/085, A61L31/14, A61L31/10, A61L31/082, C23C28/00, A61L2300/42, A61L27/34, A61L31/146, C23C28/34, A61L29/106, B05B7/205, B05B7/203, B05B7/0006, A61L27/54, C23C28/3455, A61L2420/02|
|European Classification||A61L31/16, A61L27/30R, A61L29/08B, A61L27/54, A61L27/34, A61L29/16, A61L31/10, A61L31/08B6, A61L29/10R, A61L31/08B, A61L31/14H, C23C4/00, C23C28/00, A61L31/14, C23C24/04|
|Sep 27, 2012||FPAY||Fee payment|
Year of fee payment: 4
|Nov 18, 2016||REMI||Maintenance fee reminder mailed|
|Apr 7, 2017||LAPS||Lapse for failure to pay maintenance fees|
|May 30, 2017||FP||Expired due to failure to pay maintenance fee|
Effective date: 20170407